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WO2001026799A1 - Biopuce comprenant un de reseau de capillaire et de canaux, et procedes associes - Google Patents

Biopuce comprenant un de reseau de capillaire et de canaux, et procedes associes Download PDF

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Publication number
WO2001026799A1
WO2001026799A1 PCT/US2000/027694 US0027694W WO0126799A1 WO 2001026799 A1 WO2001026799 A1 WO 2001026799A1 US 0027694 W US0027694 W US 0027694W WO 0126799 A1 WO0126799 A1 WO 0126799A1
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Prior art keywords
capillaries
capillary
reagent
plate
medial plate
Prior art date
Application number
PCT/US2000/027694
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English (en)
Inventor
Ben Hui Liu
Original Assignee
Bio-Informatics Group, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Bio-Informatics Group, Inc. filed Critical Bio-Informatics Group, Inc.
Priority to AU78692/00A priority Critical patent/AU7869200A/en
Publication of WO2001026799A1 publication Critical patent/WO2001026799A1/fr

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    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5025—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures for parallel transport of multiple samples
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
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    • B01J19/00—Chemical, physical or physico-chemical processes in general; Their relevant apparatus
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    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/502707—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the manufacture of the container or its components
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    • B01L3/508—Containers for the purpose of retaining a material to be analysed, e.g. test tubes rigid containers not provided for above
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Definitions

  • the present invention relates to biological chips for conducting parallel biosample assays and, more particularly, to a biological chip defining a channeled capillary array for conducting large-scale parallel biosample assays and associated methods of use and fabrication.
  • DNA chip technology has been a focal point of genomic scientists and potential customers of genomics technology because of the ability of the DNA chip to assay a large number of genes in parallel.
  • DNA chip technology can be used, for example, in gene expression assaying (parallel Northern blotting) to determine gene functions, in polymorphism detection and molecular marker genotyping (for example, SNP), to provide efficient genetic mapping, and, most importantly, in human disease diagnostics and in phenotype prediction for genetic manipulation of plants and animals.
  • gene expression assaying parallel Northern blotting
  • polymorphism detection and molecular marker genotyping for example, SNP
  • the Fodor chip (U.S. Patent Nos. 5,800,992 and 5,744,305) generally utilizes a flat silicon surface for in situ synthesis of the oligonucleotides on the chip surface using combinatory chemistry.
  • the Fodor chip is typically limited to short oligonucleotide lengths, where the oligos have a small number (ie: 25) of nucleotide bases.
  • the Fodor chip therefore, may also be limited by experimental error associated with on-chip oligonucleotide synthesis and with short oligonucleotide hybridization error, which is generally associated with non-specific hybridization in a relaxed condition. Thus, due to these inherent experimental errors, techniques utilizing the Fodor chip may be prone to poor experimental repeatability.
  • the Fodor chip may further be limited by slow hybridization rates due to the small effective hybridization area and random probe solution flow on the chip surface.
  • RNA amplification may also be required to increase the RNA concentration in the probe solution, which may make the Fodor chip unsuitable for certain applications, for example, monitoring gene expression.
  • procedures involving the Fodor chip may be cost inefficient due to the complexities and limitations involved in producing the chip (labor intensive and time consuming), capturing the necessary images, and analyzing the collected data.
  • the Brown chip utilizes cDNA samples disposed in a microarray on the surface of a chip comprising a glass slide.
  • the cDNA segments are typically chosen from cDNA libraries of EST sequencing projects. Each cDNA segment may range in length from several hundred to several thousand nucleotides.
  • the nucleotide sequences in the cDNA segments are generally known, though cDNA segments without nucleotide sequence information and synthetic oligos may also be used in fabricating a Brown chip.
  • the cDNA samples are usually delivered onto the chip using a robot having a three-dimensional motion control system and the ability to concurrently deposit multiple samples using a plurality of spotting pins.
  • the Brown chip may also experience limitations such as, for example, error in the x-y positioning of the spotting pins by the robot and varying amounts of the cDNA samples deposited at each spot on the chip.
  • hybridization error may be a limiting factor due to the small effective hybridization area on the chip and possibly due to secondary structure formed by single-strand oligonucleotides.
  • techniques using the Brown chip may be subject to extended hybridization times measured, for instance, in hours (for example, overnight hybridization).
  • the Brown chip may also be difficult to produce and may be limited in its practicality due to the limited surface area available on the chip.
  • the DNA samples reside on the surface of, for example, a glass slide or a silicon wafer according to both the Fodor and the Brown DNA chips.
  • the Fodor and Brown DNA chips are useful for some small-scale research in functional genomics, they are not suitable for future practical applications primarily due to high cost, time intensive fabrication of the DNA chip, and poor accuracy of experimental results.
  • the poor accuracy of a surface-based biosample assay apparatus and method typically results from the low concentration of the complementary strands of DNA (or RNA) in the probe solution and the small effective hybridization area of the spots on surface- based chips.
  • the surface-based chips such as the Brown chip
  • the surface-based chips are often prepared using a robot for transferring biosamples from a mass solution to individual spots on a glass substrate to form the microarray.
  • the biosample transfer may be accomplished, for example, by a robot operating at an overall rate of about four dots per second. Since a microarray may include, for instance, multiple thousands of individual samples, a microarray may be prone to lengthy formation times as well as possible contamination due to the robotic system.
  • the DNA chip should be capable of producing more accurate and repeatable experimental results than current prior art DNA chips.
  • a biochip adapted to interact with a liquid reagent comprising a plate defining a plurality of cylindrical capillaries and a plurality of channels oriented substantially perpendicularly to the capillaries and configured to selectively operably connect adjacent capillaries.
  • At least one capillary comprises a reagent inlet and at least one capillary comprises a reagent outlet.
  • the channels operably connect adjacent capillaries so as to form a continuous passage from the reagent inlet to the reagent outlet through each of the capillaries.
  • the channels are configured such that the reagent flow is directed into a capillary at one end thereof.
  • the reagent flow is then directed from the capillary at the other end thereof such that the reagent flows through substantially the length of the capillary.
  • the channels operably connect adjacent capillaries such that the reagent is directed to tlow serially through all of the capillaries.
  • Another advantageous aspect of the present invention comprises a method of fabricating a biochip defining a plurality of connected capillaries.
  • a medial plate having a pair of opposed surfaces is formed.
  • the medial plate defines a plurality of cylindrical capillaries, with each capillary having a pair of opposed ends.
  • a pair of end plates is then formed, with each end plate being configured to operably engage one of the opposed surfaces of the medial plate.
  • Each end plate further defines a series of channels configured so as to be oriented substantially perpendicularly to the capillaries. The channels are further configured to selectively connect adjacent capillaries at the ends thereof when the end plates are operably engaged with the medial plate.
  • a further advantageous aspect of the present invention comprises a method of fabricating a biochip defining a plurality of connected capillaries. First, a mold defining a medial plate having a pair of opposed surfaces is provided. The mold further includes a plurality of cylindrical rods each having a pair of opposed ends.
  • the rods are further operably connected by a series of connecting members oriented substantially perpendicularly to the rods about the opposed surfaces of the medial plate and selectively connecting adjacent rods at the ends thereof.
  • a polymeric material is then introduced into the mold such that the polymer is molded into and forms the medial plate, wherein the medial plate thereby defines a plurality of capillaries corresponding to the rods and a plurality of channels corresponding to the connecting members.
  • the opposed surfaces of the medial plate are sealed with the corresponding end plates so as to form a continuous passage from a reagent inlet capillary to a reagent outlet capillary.
  • the passage further extends substantially the length of each capillary and serially through all of the capillaries defined by the medial plate.
  • a further advantageous aspect of the present invention comprises an alternate method of fabricating a biochip defining a plurality of connected capillaries.
  • a plurality of cylindrical capillaries is etched in a medial plate having a pair of opposed surfaces, wherein each capillary has a pair ot opposed ends.
  • a plurality of channels, oriented substantially perpendicularly to the capillaries, is then selectively etched between adjacent capillaries on each of the opposed surfaces of the medial plate.
  • the opposed surfaces of the medial plate are then sealed with the corresponding end plates so as to form a continuous passage from a reagent inlet capillary to a reagent outlet capillary.
  • the passage further extends substantially the length of each capillary and serially through all of the capillaries defined by the medial plate.
  • a still further advantageous aspect of the present invention comprises a method of conducting multiple sample parallel bioassays.
  • a biochip defines a plurality of cylindrical capillaries having opposed ends and being selectively operably connected by a series of channels oriented substantially perpendicularly thereto and about the ends thereof so as to form a continuous passage from a reagent inlet capillary to a reagent outlet capillary.
  • the passage extends substantially the length of each capillary and serially through all of the capillaries defined by the biochip.
  • a biosample is then immobilized on the inner walls of each of the capillaries before a liquid reagent is flowed through the passage from the reagent inlet capillary to the reagent outlet capillary, through each of the capillaries, so as to assay the biosamples.
  • the DNA chip according to embodiments of the present invention may be expediently fabricated in a timely and cost-effective manner.
  • the biosamples are immobilized on the walls of the capillaries. Since the biosamples adhere to the inner walls of the capillaries, the effective hybridization area is increased compared to surface-based biochips which have lower effective hybridization areas.
  • the increased effective hybridization area facilitates detection of lower concentrations of the assayed biosample by providing a strong hybridization signal.
  • the closed reagent flow system of the biochip according to the present invention allows the reagent probe solution flow to be more precisely controlled, thus requiring a relatively small amount of the reagent solution to provide acceptable hybridization compared to surface-based biochips. Still further, once the biochip according to the present invention is prepared with the biosamples, the biochip can be sealed and a reagent probe solution flowed in different direction and at different rates from an inlet capillary to an outlet capillary in a closed system.
  • the closed system and controlled flow of the reagent probe solution provides an increased hybridization rate with less false hybridization and less secondary structure disturbance as compared to surface-based biochips.
  • the DNA chip according to the present invention is capable of providing more accurate and repeatable results due to the tighter control over critical parameters.
  • FIG. 1 is a perspective view of a biochip according to one embodiment of the present invention.
  • FIG. 2 is a perspective view of a capillary defined by a biochip according to one embodiment of the present invention.
  • FIG. 3 is a cross-sectional view of a biochip according to one embodiment of the present invention with corresponding plan views of the upper and lower surfaces of the biochip.
  • FIGS. 3A-1 to 3A-4 are various views of a medial plate, two opposed end plates, and a securing member comprising a biochip according to one embodiment of the present invention.
  • FIG. 4 is a schematic of the electrostatic fluid flow system according to one embodiment of the present invention.
  • FIG. 5 is a flowchart of a method of fabricating a biochip according to one embodiment of the present invention.
  • FIG. 6 is a flowchart of an alternate method of fabricating a biochip according to one embodiment of the present invention.
  • FIG. 7 is a flowchart of still another alternate method of fabricating a biochip according to one embodiment of the present invention.
  • FIG. 7A is a perspective view of the plate and plan views of the top and bottom surfaces thereof, with the corresponding masks for producing each portion, in accordance with one embodiment of the present invention.
  • FIG. 8 is a flowchart of a method of performing a multiple sample parallel bioassay in accordance with one embodiment of the present invention.
  • DETAILED DESCRIPTION OF THE INVENTION The present invention now will be described more fully hereinafter with reference to the accompanying drawings, in which preferred embodiments of the invention are shown. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art. Like numbers refer to like elements throughout. FIGS.
  • the biochip 10 generally comprises a plate 20 having an upper surface 30 and a lower surface 40, a plurality of capillaries 50 defined by the plate 20, and a plurality of channels 60 selectively and operably connecting adjacent capillaries 50.
  • the plate 20 is, for instance, about one centimeter wide by one centimeter long by one-half millimeter thick.
  • the capillaries 50 have, for example, an inner diameter of about 20 microns with about 80 micron spaces between adjacent capillaries 50 such that up to 10,000 capillaries 50 may be fabricated in one biochip 10.
  • the capillaries 50 are generally disposed about the plate 20 in an array, though many different configurations may also be used. Accordingly, it will be understand that the dimensions and configurations of the plate 20 and the capillaries 50 may vary widely in accordance with the requirements of particular situations consistent with the spirit and scope of the present invention.
  • the plate 20 may be on the order of approximately ten centimeters wide by ten centimeters long by three millimeters thick.
  • the capillaries 50 may vary, for example, between about 5 microns and about 1000 microns in diameter. As shown in FIG. 2, the capillaries 50 further generally increase the effective hybridization surface area of the biochip 10 compared to surface-based biochips using samples comprising a spot on a flat surface. For instance, for a capillary 50 having a diameter equal to the diameter of the spot, the capillary 50 provides a hybridization surface area advantage equal to the ratio of four times the height of the capillary 50 to the diameter of the spot.
  • the capillary 50 provides about 100 times the hybridization surface area as compared to a 20 micron diameter spot on a surface- based biochip.
  • a larger hybridization area provides a stronger hybridization signal, increases the hybridization rate, and tends to indicate less false hybridization.
  • the larger hybridization area tends to reduce the likelihood of secondary structure disturbance since the chance of DNA molecules forming secondary structure is inversely proportional to the hybridization surface area.
  • the channeled capillary array biochip 10 would be 100 times less likely to experience DNA secondary structure disturbance than a surface-based biochip.
  • the plate 20 is comprised of a semiconductor material such as, for example, silicon.
  • a silicon biochip 10 uses, for instance, common semiconductor photolithography and etching processes to form the capillaries 50 in the plate 20. More particularly, a layer of a photosensitive polymer (not shown) is deposited on a surface of the plate 20 and patterned to define a plurality of holes therein corresponding in the size and distribution to the desired capillaries 50. The patterned layer thus comprises a mask (not shown) for forming the capillaries 50. Once the mask is formed, the silicon plate 20 is etched through the holes in the mask to form the plurality of capillaries 50.
  • the biochip 10 may be comprised of a plastic or other polymer material. Where a plastic material is used to form the biochip 10, a mold is prepared such that the plastic may be, for instance, injection molded to form the plate 20.
  • the capillaries 50 are generally symmetrically and evenly disposed about the plate 20 and extend from the upper surface 30 to the lower surface 40 thereof. Lateral channels 60 are further formed in the plate 20 to selectively operably connect adjacent capillaries 50 about both the upper surface 30 and the lower surface 40.
  • orientation-related references used herein, such as “upper,” “lower,” and “lateral,” are used for example only in reference to the corresponding figures. It will be understood that a biochip according to embodiments of the invention may be configured in many different orientations wherein such a reference frame may not be applicable.
  • tne capillaries 50 are each connected to one adjacent capillary 50 on the upper surface 30 by a channel 60 and to a different capillary 50 on the lower surface 40 by another channel 60.
  • the channels 60 operably connect adjacent capillaries 50 such that a single continuous passage is formed between at least one reagent inlet capillary 52 and at least one reagent outlet capillary 54.
  • the fluid would be directed along the length of the reagent inlet capillary 52, through a channel 60 on the lower surface 40 to an adjacent capillary 50, and then along the length of that capillary 50 before being directed through still another channel 60 on the upper surface 30 to another adjacent capillary 50. This process continues until the fluid is directed serially through all of the capillaries 50 and along the length of the reagent outlet capillary 54.
  • the plate 20 may be formed such that the channels 60 operably connecting adjacent capillaries 50 on both the upper surface 30 and the lower surface 40 are open with respect to the upper and lower surfaces 30 and 40.
  • the open upper surface 30 and lower surface 40 permit access to the capillaries 50 and facilitate immobilization of the biosample on the inner walls 56 of the capillaries 50.
  • the glass plates 70 seal the upper surface 30 and the lower surface 40 of the plate 20 such that the ends of the capillaries 50 are sealed and any fluid flowing through the capillary 50 is directed into and out of the capillary 50 by the channels 60. Accordingly, a fluid, such as the probe solution, is able to flow from the reagent inlet capillary 52 to the reagent outlet capillary 54 along a continuous passage between adjacent capillaries 50, and serially through each capillary 50 in the plate 20, to the reagent outlet capillary 54.
  • a fluid such as the probe solution
  • Appropriate mechanisms are preferably provided in the glass plate 70 sealed to the upper surface 30 (or lower surface 40) of the plate 20 to allow the flow of a reagent probe solution through the glass plate 70 into the reagent inlet capillary 52 and from the reagent outlet capillary 54.
  • a biochip 10 may be fabricated in many different configurations consistent with the spirit and scope of the present invention, ror example, as shown in FIGS. 3A-1 to 3A-4, the biochip 10 may be fabricated so as to comprise a medial plate 25 as shown in FIG. 3A-1, corresponding end plates 35 and 45 as shown in FIGS. 3A-2 and 3A-3, respectively, and a securing member 75 as shown in FIG. 3A-4.
  • the medial plate 25 defines a plurality of capillaries 50 that extend between the upper and lower surfaces 30 and 40 as shown in FIG. 3A-1.
  • a top end plate 35 is configured to have a surface 34 for engaging the top surface 30 of the medial plate 25.
  • the surface 34 further defines a series of channels 60, each configured to extend between adjacent capillaries 50 of the medial plate 25.
  • At least one channel 60 comprises a reagent inlet channel 33 corresponding to the reagent inlet capillary 52 and at least one channel 60 comprises a reagent outlet channel 32 co ⁇ esponding to the reagent outlet capillary 54.
  • a bottom end plate 45 is also configured to have a surface 44 for engaging the bottom surface 40 of the medial plate 25.
  • the surface 44 further defines a series of channels 60, each also configured to extend between adjacent capillaries 50 of the medial plate 25.
  • the channels 60 in the respective end plates 35 and 40 engage the corresponding capillaries 50 in the medial plate 25 so as to form a continuous passage extending serially through all of the capillaries 50, and along the length of each, from the reagent inlet channel 32 to the reagent outlet channel 33.
  • a securing member 75 in one instance, a "C" shaped section, engages corresponding tracks 31 and 41 in the end plates 35 and 45, respectively, (wherein two such securing members 75 are used in the illustrated embodiment) to maintain a sealing relation between the end plates 35 and 45 and the medial plate 25.
  • a securing member 75 in one instance, a "C" shaped section, engages corresponding tracks 31 and 41 in the end plates 35 and 45, respectively, (wherein two such securing members 75 are used in the illustrated embodiment) to maintain a sealing relation between the end plates 35 and 45 and the medial plate 25.
  • the sealing relation between the end plates 35 and 45 and the medial plate 25 may be accomplished by many different forms of connecting members or other appropriate mechanisms consistent with the spirit and scope of the present invention.
  • the reagent probe solution flow originates from and returns to a hybridization chamber (not shown) connected to the reagent inlet capillary 52 and the reagent outlet capillary 54, thereby forming a closed system for a flow of the reagent.
  • a hybridization chamber (not shown) connected to the reagent inlet capillary 52 and the reagent outlet capillary 54, thereby forming a closed system for a flow of the reagent.
  • Having a closed reagent flow system generally permits a lower quantity of the reagent solution to be used compared to surface-based biochips. For example, a maximum RNA concentration can be attained with 0.1 microliters of a reagent probe solution. In contrast, the Brown chip requires more than 10 microliters of the reagent solution to carry out the hybridization reactions using a surface-based biochip configuration.
  • "pumping" of the reagent probe solution through the capillary 50 may be accomplished using electrostatic pressure generated by a voltage applied across the two ends of a capillary 50.
  • high voltage of, for example, l-20kV is required to generate the necessary pressure.
  • electrostatic pressure By using electrostatic pressure to pump the reagent probe solution through the continuous passage formed by the capillaries 50 and the channels 60, the voltage may be readily reversed such that the system is capable of pumping the reagent probe solution in the opposite direction.
  • Alternating directions of the reagent probe solution flow may thereby allow a more complete and faster hybridization process compared to surface-based biochips. For example, several reversals of reagent flow may be necessary to obtain complete hybridization.
  • the movement of molecules by the application of a plurality of electrical fields is further described in U.S. Patent No. 5,126,022 to Soane et al, the contents of which are herein incorporated by reference.
  • the total number of collisions between the DNA fragments in the biosample and the complementary strand in the probe solution is a function of the hybridization area, the concentration of the complementary strand in the probe solution, and the velocity of the DNA molecules in the probe solution.
  • control of the flow rate of the probe solution is advantageous compared to the random flow used by surface-based biochips.
  • the use of small diameter capillaries 50 with controlled flow of the probe solution further increases effective concentration of the complementary RNA strands.
  • the effective concentration of the RNA strands in the probe solution may be up to 300,000 times greater than a comparable a surface-based biochip.
  • control of the probe solution flow and the higher effective hybridization area provides more complete hybridization, with a higher hybridization rate, and reduces the amount of the probe solution required to perform the assay.
  • the time necessary to complete a hybridization procedure may be on the order of minutes as compared to hours of hybridization time that may be required for surface-based biochips.
  • Another advantageous aspect of the present invention comprises a method of fabricating a biochip defining a plurality of connected capillaries, as shown in FIG. 5.
  • a medial plate 25 having a pair of opposed surfaces 30 and 40 is first formed (block 100).
  • the medial plate 25 generally defines a plurality of cylindrical capillaries 50 with each capillary having a pair of opposed ends.
  • a pair of end plates 35 and 45 is then formed (block 105), wherein each end plate 35 and 45 is configured to operably engage one of the opposed surfaces 30 and 40 of the medial plate 25.
  • Each end plate 35 and 45 further defines a series of channels 60 configured so as to be oriented substantially perpendicularly to the capillaries 50 such that the channels selectively connect adjacent capillaries 50 at the ends thereof when the end plates 35 and 45 are engaged with the medial plate 25.
  • the end plates 35 and 45 are then secured to the opposed surfaces 30 and 40 of the medial plate 25 (block 110) so as to form a continuous passage extending substantially the length of each capillary 50 and serially through all of the capillaries 50.
  • Still another advantageous aspect of the present invention comprises a method of fabricating a biochip defining a plurality of connected capillaries as shown in FIG. 6.
  • a mold is first provided which defines a medial plate 25 having a pair of opposed surfaces 30 and 40 (block 115).
  • the mold further includes a plurality of cylindrical rods with each rod having a pair of opposed ends.
  • the mold includes a series of connecting members oriented substantially perpendicularly to the rods about the opposed surfaces of the medial plate 25 and selectively connecting adjacent rods at the ends thereof.
  • a polymeric material is introduced into the mold such that the polymer forms the medial plate 25 (block 120). This process of forming the medial plate 25 may be accomplished by, for example, using an injection molding process.
  • the medial plate 25 may be comprised of, for example, polycarbonate. Once the polymer has been injected into the mold and solidifies, the mold is removed and the medial plate 25 released (block 125). The upper surface 30 and the lower surface 40 of the medial plate 25 are then sealed (block 130), for example, by corresponding end plates, such as glass plates 70, so as to form a continuous passage between the plurality of capillaries 50 such that the passage directs the reagent solution flow from the reagent inlet capillary 52 to the reagent outlet capillary 54. The passage extends substantially the length of each capillary 50 and serially through all of the capillaries 50 defined by the medial plate.
  • the mold may be configured such that the medial plate 25 defines the capillaries 50 while the end plates 35 and 45 define the connecting channels 60 as previously described in conjunction with FIGS. 3A-1 to 3A-4.
  • a method according to the described embodiment may be altered so as to form various combinations of components which, when assembled, form a biochip 10 according to the configurations described herein.
  • the biochip 10 includes a low to medium density of capillaries 50, wherein a low density biochip 10 may be on the order of up to 200 capillaries per square centimeter, and a medium density biochip 10 may include up to 2,000 capillaries per square centimeter.
  • Still a further advantageous aspect of the present invention comprises an alternate method of fabricating a biochip defining a plurality of connected capillaries, as shown in FIG. 7.
  • a plurality of cylindrical capillaries 50 is first etched in a medial plate 25 having a pair of opposed surfaces wherein the capillaries 50 each have a pair of opposed ends (block 135).
  • a plurality of channels 60 between adjacent capillaries 50 is then selectively etched on each of the upper surface 30 and the lower surface 40 of the medial plate 25 such that the channels 60 are oriented substantially perpendicularly to the capillaries 50 (block 140).
  • the upper surface 30 and the lower surface 40 of the medial plate 25 are then sealed (block 145) with corresponding end plates so as to form a continuous passage from a reagent inlet capillary 52 to a reagent outlet capillary 54.
  • the passage generally extends substantially the length of each capillary 50 and serially through all of the capillaries 50 defined by the medial plate 25.
  • the method according to this embodiment is particularly advantageous where the biochip 10 requires a high density of capillaries 50, wherein a high density biochip 10 includes up to 200,000 capillaries per square centimeter.
  • High density biochips 10 may be made of a semiconductor material such as, for instance, silicon, which thereby allows semiconductor fabrication techniques to be applied to form the capillaries 50 and channels 60. As shown in FIG. 7A, a flat plate 99
  • the mask 80 can be used to define the circles 82 corresponding to the locations of the capillaries 50 in the desired configuration thereof such as, for example, an array.
  • the patterned photoresist is then removed such that the photoresist layer remaining on the plate 20 defines a plurality of circles in the desired locations of the capillaries 50.
  • the plate 20 is then exposed to an etching process such that the areas within the circles defined by the photoresist are removed and the capillaries 50 formed through the thickness of the plate 20.
  • This process allows fine capillaries 50 with close spacing therebetween to be produced through the plate 20, thereby providing a high density biochip 10 for accommodating a larger amount of biosamples to be assayed.
  • the photoresist layer is removed.
  • a second photoresist layer is then applied to one of the upper surface 30 and the lower surface 40 and patterned with a mask 84 to define a plurality of lateral channels 60 connecting adjacent capillaries 50.
  • the plate 20 is then exposed to another etching process which produces shallow trenches in the surface of the plate 20 between the selected capillaries 50.
  • Yet another advantageous aspect of the present invention comprises a method of conducting multiple sample parallel bioassays, as shown in FIG. 8.
  • a biochip 10 is first provided defining an array comprising a plurality of cylindrical capillaries 50 having opposed ends and being selectively operably connected by a series of channels 60 oriented substantially perpendicularly thereto and about the ends thereof so as to form a continuous serial passage between capillaries 50 from a reagent inlet capillary 52 to a reagent outlet capillary 54 (block 150).
  • a biosample is then immobilized on the inner walls 56 of the capillaries 50 (block 155) before a reagent solution is flowed from the reagent inlet capillary 52 to the reagent outlet capillary 54 through each of the capillaries 50 to facilitate the hybridization reaction ana to assay the biosamples (block 160).
  • a scanner may be used to detect and capture bioassay signals.
  • the bioassay signals may be detected and captured electronically through sensors and/or circuits fabricated in the biochip 10.
  • a biochip according to the present invention provides a large hybridization area for conducting bioassays by using the wall of a cylindrical capillary on which to immobilize the samples. Further, high hybridization rates are obtained due to the controllability of the reagent probe solution flow and the large effective hybridization area, particularly when a high RNA concentration is used in the reagent probe solution. Accordingly, a faster and more complete hybridization process is realized. A biochip according to the present invention can thus be produced in a timely and cost-effective manner.
  • preparation of a biochip according to the present invention is facilitated by the capillary configuration, which is less sensitive to error associated with application of the biosample to the biochip than surface-based biochips.

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Abstract

L'invention concerne une biopuce (10) comprenant une plaque (20) qui définit une pluralité de capillaires (50) cylindriques, dont chacun comprend deux extrémités opposées, et une pluralité de canaux (60) sensiblement perpendiculaires aux capillaires (50) et conçus de manière à relier sélectivement, de manière fonctionnelle, les capillaires (50) adjacents. Au moins un capillaire (50) comprend une entrée (52) pour réactif et au moins un capillaire (50) comprend une sortie (54) réactif. Les canaux (60) relient de manière fonctionnelle les capillaires (50) adjacents de manière à former un passage continu entre l'entrée (52) et la sortie (54) du réactif à travers chaque capillaire (50). Ces canaux sont conçus de manière qu'à une de leurs extrémités le flux de réactif est dirigé dans un capillaire (50). Le flux de réactif est ensuite dirigé vers l'autre extrémité du capillaire (50) de sorte que le réactif traverse sensiblement la longueur du capillaire (50). Les canaux (60) relient de manière fonctionnelle les capillaires (50) adjacents de manière à diriger l'écoulement du réactif de manière continue à travers tous les capillaires (50). L'invention concerne en outre un procédé d'utilisation de cette de cette biopuce, ainsi que plusieurs procédés associés permettant de produire ces biopuces.
PCT/US2000/027694 1999-10-08 2000-10-06 Biopuce comprenant un de reseau de capillaire et de canaux, et procedes associes WO2001026799A1 (fr)

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US60/158,518 1999-10-08

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Cited By (5)

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Publication number Priority date Publication date Assignee Title
WO2003064703A1 (fr) * 2002-01-28 2003-08-07 Bio-Informatics Group, Inc. Modele de biopuce a quatre dimensions pour applications a haut rendement, et procedes d'utilisation correspondants
WO2004072620A1 (fr) * 2003-02-06 2004-08-26 Applera Corporation Dispositifs et procedes de preparation d'echantillons biologiques
US6900133B2 (en) 2002-09-18 2005-05-31 Applied Materials, Inc Method of etching variable depth features in a crystalline substrate
US7338760B2 (en) 2001-10-26 2008-03-04 Ntu Ventures Private Limited Sample preparation integrated chip
CN106345547A (zh) * 2016-11-08 2017-01-25 常州锐德医疗科技有限公司 一种微流控芯片

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US5567294A (en) * 1996-01-30 1996-10-22 Board Of Governors, University Of Alberta Multiple capillary biochemical analyzer with barrier member
US5580523A (en) * 1994-04-01 1996-12-03 Bard; Allen J. Integrated chemical synthesizers
US5759779A (en) * 1995-08-29 1998-06-02 Dehlinger; Peter J. Polynucleotide-array assay and methods
WO1999013313A1 (fr) * 1997-09-11 1999-03-18 Genovations, Inc. Procede de production de reseaux a haute densite
WO1999032219A1 (fr) * 1997-12-19 1999-07-01 Glaxo Group Limited Systemes et procedes de synthese parallele en phase solide

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US5580523A (en) * 1994-04-01 1996-12-03 Bard; Allen J. Integrated chemical synthesizers
US5759779A (en) * 1995-08-29 1998-06-02 Dehlinger; Peter J. Polynucleotide-array assay and methods
US5567294A (en) * 1996-01-30 1996-10-22 Board Of Governors, University Of Alberta Multiple capillary biochemical analyzer with barrier member
WO1999013313A1 (fr) * 1997-09-11 1999-03-18 Genovations, Inc. Procede de production de reseaux a haute densite
WO1999032219A1 (fr) * 1997-12-19 1999-07-01 Glaxo Group Limited Systemes et procedes de synthese parallele en phase solide

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7338760B2 (en) 2001-10-26 2008-03-04 Ntu Ventures Private Limited Sample preparation integrated chip
WO2003064703A1 (fr) * 2002-01-28 2003-08-07 Bio-Informatics Group, Inc. Modele de biopuce a quatre dimensions pour applications a haut rendement, et procedes d'utilisation correspondants
US6924107B2 (en) 2002-01-28 2005-08-02 Bio-Informatics Group, Inc. Four dimensional biochip design for high throughput applications and methods of using the four dimensional biochip
US6900133B2 (en) 2002-09-18 2005-05-31 Applied Materials, Inc Method of etching variable depth features in a crystalline substrate
WO2004072620A1 (fr) * 2003-02-06 2004-08-26 Applera Corporation Dispositifs et procedes de preparation d'echantillons biologiques
CN106345547A (zh) * 2016-11-08 2017-01-25 常州锐德医疗科技有限公司 一种微流控芯片

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